CN114376559B - Respiratory datum line tracking acceleration method - Google Patents
Respiratory datum line tracking acceleration method Download PDFInfo
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- CN114376559B CN114376559B CN202210052104.1A CN202210052104A CN114376559B CN 114376559 B CN114376559 B CN 114376559B CN 202210052104 A CN202210052104 A CN 202210052104A CN 114376559 B CN114376559 B CN 114376559B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/087—Measuring breath flow
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7225—Details of analog processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/40—Respiratory characteristics
Abstract
The invention provides a method for accelerating and tracking a reference line of a breathing signal of a user in a breathing assistance system, which is used for accelerating and tracking the breathing reference line when the operation of the user or the state of wearing a breathing mask changes. The tracking method includes tracking relatively high points of the respiratory signal during an inspiratory cycle, tracking relatively low points of the respiratory signal during an expiratory cycle, and calculating a respiratory amplitude for the interval. According to the invention, the respiration amplitude is calculated as a basis, and the speed of tracking the respiration datum line is optimized after the reference value is obtained through calculation.
Description
Technical Field
The invention relates to a calculation method of a breathing reference line, in particular to a breathing reference line tracking acceleration method for a positive pressure respirator.
Background
Methods of treating sleep apnea include surgery, mouth occluders, positive airway pressure (CPAP), etc., wherein positive airway pressure may also be used to treat: chronic obstructive pulmonary disease, congestive heart failure, neuromuscular disorders, and the like. The positive pressure respirator can prop open the upper respiratory tract which can collapse by air pressure so as to maintain the smoothness of the respiratory tract, and can treat the problems of snoring, apnea and the like. The automatic type positive pressure respirator has an air flow Sensor (airlow Sensor) to sense whether the user is currently exhaling or inhaling, so that the automatic type positive pressure respirator can automatically change the air pressure according to the breathing state of the user.
The breathing state of the user in each stage of a breathing cycle can be respectively represented by breathing phases, so that the user has a plurality of breathing phases in a breathing cycle, and the breathing apparatus should respectively execute corresponding control and measurement items when in different breathing phases, for example: various pressures and various flow rates of the air flow output/input; however, the respiratory phase is only a generic term, and there is no fixed design or specification of the number of phases that should be provided, generally according to the design of the developer, and because the respiratory state of the user can be at least divided into inspiration and expiration, the respiratory phase is usually designed to be a number greater than 2, for example: 4-phase, 6-phase …, etc.
The breathing reference line is an important reference basis for the positive pressure respirator to judge the breathing phase of the user. The judgment of the breathing phase can influence the time point of controlling the output/input of the air flow, and the early judgment can improve the probability of misjudgment, so that a user of the respirator feels uncomfortable; too slow a determination may result in a user having a non-compliant inhalation or a non-compliant exhalation and may also result in a user being uncomfortable. Therefore, the signal stability and response speed of the breathing reference line are important problems for controlling the positive pressure respirator.
The respiratory reference line is usually generated by using a digital filter or an averaging algorithm, where the digital filter is as follows: finite Impulse Response (FIR) or Infinite Impulse Response (IIR) can respond faster to changes in respiratory baseline, but is relatively complex in design, not only requiring high computational effort, but also potentially compromising signal integrity. And averaging methods such as: the exponential averaging method (Exponential Moving Average, EMA) or the simple averaging method (Simple Moving Average, SMA), although having a low computational complexity, often causes a delay in the response of the breathing reference line due to an increase in the number of points or cycles used to calculate the average. In the prior art US 7,337,778 B2, a long and a short average line are used in combination with a threshold setting as a basis for accelerating the adjustment of the breathing reference line, wherein the determination time is set to 6 seconds (i.e. one breathing cycle).
Whether the filter or the averaging method is adopted, too high points or cycles may cause too slow response of the breathing reference line, so that the operation of the positive pressure respirator cannot meet the requirement, but too low points or cycles also cause the calculation result of the breathing reference line to be easily disturbed by noise interference, thereby affecting the accuracy of the breathing phase judgment of the user. In addition, the respiratory rate may vary with the degree of sleep, and other sleep events may cause instantaneous flow changes, so that the design of the fixed point number or the fixed cycle number is difficult to be integrally applied. In view of the recent trend of the increasing number of users of respirators, there is a strong need for how to achieve "rapid adjustment of the respiratory reference line" so that the respiratory phase of the user can be accurately determined.
Disclosure of Invention
In view of the above problems, the present invention discloses a respiratory datum line tracking acceleration method, which is applied to a respiratory assistance system to optimize a tracking speed of a respiratory datum line, and comprises the following main technical contents:
a breath baseline tracking acceleration method provides a calculation module and receives a breath flow signal, the breath baseline tracking acceleration method comprises:
step S1: the calculation module generates a respiratory amplitude and a respiratory datum line according to the respiratory flow signal;
step S2: the calculation module generates a respiratory phase judgment signal according to the respiratory flow signal and the respiratory datum line, when the respiratory phase judgment signal stays at a respiratory phase exceeding a time threshold, the flow jumps to step S3, and when the respiratory phase judgment signal stays at a respiratory phase not exceeding the time threshold, the flow jumps back to step S1;
step S3: judging whether a modulation triggering condition is met, if so, jumping to the step S4, and if not, jumping back to the step S1;
step S4: the calculation module generates a respiration datum line reference value according to the product of the respiration amplitude and a proportional parameter and a relatively low point in the respiration datum line;
step S5: the calculation module corrects the breathing datum according to the breathing datum reference value.
Preferably, any one of the following trigger conditions is satisfied when the modulation trigger condition is satisfied:
amplitude modulation triggering conditions: the difference between two consecutive breath amplitudes in the breath baseline is greater than a breath amplitude threshold;
high point modulation trigger conditions: the difference between two consecutive relatively high points in the respiratory datum line is greater than a respiratory high point threshold;
low point modulation trigger conditions: the difference between two consecutive relatively low points in the respiratory datum is greater than a respiratory low point threshold;
baseline modulation triggering conditions: the difference between two consecutive points in the respiratory datum is greater than a respiratory datum threshold; and is also provided with
Each of the breath amplitude threshold, the breath high point threshold, the breath low point threshold, and the breath baseline threshold is a product of the breath amplitude and a proportional parameter.
Preferably, the respiratory flow signal may be a real-time measured flow signal, a filtered flow signal, or a patient respiratory signal obtained by processing a measured signal.
Preferably, in the foregoing respiratory reference line tracking acceleration method, the respiratory reference line reference value is calculated by:
the respiratory datum reference value Bref n ＝PoleL n +FlowPP n-1 ×P ref The datum line reference value parameter P ref Between 1% and 99% Polel n To be the current relatively low point in the respiratory baseline, flowPP n-1 For the previous respiratory amplitude in the respiratory baseline, wherein foot code n represents the current value and foot code n-1 represents the previous value.
Preferably, in the foregoing respiratory reference line tracking acceleration method, the calculation formula of the corrected respiratory reference line value is:
the corrected respiratory baseline value BnewN= (Bref) n -Base n-1 )×P BL +Base n-1 The reference line modulating parameter P BL Between 1% and 99% Base n-1 Is the previous value of the respiratory datum line.
Drawings
FIG. 1 is a block diagram of a calculation module of a respiratory baseline tracking acceleration method according to the present invention.
Fig. 2A is a schematic diagram of an exponential smooth moving average line (abbreviated as long period EMA) of a user respiratory airflow signal for 30 periods.
Fig. 2B is a schematic diagram of an exponential smooth moving average line (short period EMA) of 10 periods of the user respiratory airflow signal.
FIG. 2C is an exponential smooth moving average line (short long period EMA) of the respiratory Flow signal Flow of FIG. 2A for 30 periods
Fig. 3A shows a system respiratory Flow rate, a respiratory reference line of long-period EMA, and a respiratory Flow rate signal Flow with respect to a time axis when a respiratory reference line tracking acceleration method of the present invention is not used and air leakage is started.
Fig. 3B is a respiratory phase determined according to fig. 3A.
Fig. 4A shows the system respiratory Flow, the respiratory reference line of the long-period EMA, and the respiratory Flow signal Flow with respect to the time axis when the respiratory reference line tracking acceleration method of the present invention is not used and the leak is recovered to be normal.
Fig. 4B is a breathing phase determined according to fig. 4A.
Fig. 5A shows the system respiratory Flow, respiratory Flow signal Flow, respiratory baseline and baseline reference values when the method of the present invention is applied to long-period EMA and there is a leak.
Fig. 5B is the breathing phase determined according to fig. 5A.
Fig. 6A shows a system respiratory Flow, respiratory Flow signal Flow and respiratory reference line for the long period EMA to recover from leakage.
Fig. 6B is a respiratory phase determined according to fig. 6A.
FIG. 7 is a flowchart of the algorithm of the respiratory baseline tracking acceleration method of the present invention.
FIG. 8 is a block diagram of a computing module of another embodiment of a respiratory baseline tracking acceleration method according to the present invention.
Detailed Description
The technical means adopted by the invention to achieve the preset aim are further described below by matching the specification, the drawings and the preferred embodiments of the invention.
Referring to fig. 1, fig. 1 shows a calculation module 10 for executing the respiratory reference line tracking acceleration method of the present invention, wherein the calculation module 10 includes a respiratory signal unit 11, a high-low point determination unit 12 connected to the respiratory signal unit 11, a respiratory reference line unit 13 connected to the respiratory signal unit 11, an amplitude determination unit 14 connected to the high-low point determination unit 12, a respiratory reference line reference value unit 15 connected to the high-low point determination unit 12 and the amplitude determination unit 14, a respiratory reference line correction unit 16 connected to the respiratory reference line unit 13 and the respiratory reference line reference value unit 15, respectively, and a phase detection unit 17 connected to the respiratory signal unit 11 and the respiratory reference line correction unit 16, respectively. The computing module 10 is comprised of a computer hardware such as a personal computer, mobile device or server, and an algorithm running on the computer hardware.
The respiratory signal unit 11 is mainly configured to obtain a system respiratory Flow of the positive pressure respirator and obtain a respiratory Flow signal Flow close to the respiratory Flow of the user after system correction, where the respiratory Flow signal Flow is a time function, and the respiratory Flow signal Flow may be a real-time measured Flow signal, a filtered Flow signal, or a patient respiratory signal obtained after processing the measured signal according to different system correction modes.
The high-low point determination unit 12 receives the respiratory Flow signal Flow and determines a relatively high point PoleH and a relatively low point PoleL in the respiratory Flow signal Flow according to the respiratory Flow signal Flow, wherein the relatively high point PoleH and the relatively low point PoleL are both Time series (Time series).
In the inspiration process, according to the turning of the respiratory Flow signal Flow, a relatively high point PoleH of the respiratory Flow signal Flow is obtained, wherein the common way of capturing the relatively high point PoleH is as follows: monitoring a maximum value of the respiratory Flow signal Flow or a slope of the respiratory Flow signal Flow over a period of time from a positive value to a negative value.
In the process of breathing, according to the turning of the respiratory Flow signal Flow, a relatively low point PoleL of the respiratory Flow signal Flow is obtained, wherein the common method for capturing the relatively low point PoleL is as follows: monitoring a minimum value of the respiratory Flow signal Flow or a slope of the respiratory Flow signal Flow over a period of time changes from a negative value to a positive value.
The respiratory reference line unit 13 also receives the respiratory Flow signal Flow and generates a respiratory reference line according to the respiratory Flow signal Flow, and the algorithm for calculating the respiratory reference line is usually a digital filter or an averaging method as described above.
The amplitude determining unit 14 receives the relatively high point PoleH and the relatively low point PoleL and generates a respiration amplitude FlowPP according to the received values, wherein the respiration amplitude FlowPP is a time function.
The respiratory reference line reference value unit 15 receives the respiratory amplitude FlowPP and the relatively high point PoleH and the relatively low point PoleL, and generates a respiratory reference line reference value according to the respiratory amplitude FlowPP and the relatively high point PoleH and the relatively low point PoleL, wherein the respiratory reference line reference value is a time function.
The breathing reference line correction unit 16 receives the breathing reference line reference value and the breathing reference line, and generates a corrected breathing reference line accordingly. The phase detecting unit 17 receives the corrected breathing reference line value and the breathing Flow signal Flow, and generates a breathing phase determining signal accordingly.
Referring to fig. 2A to 2C, fig. 2A is a respiratory Flow signal Flow with respect to a time axis, fig. 2B is an exponential smooth movement average line (short period EMA) of 10 periods of the respiratory Flow signal Flow in fig. 2A, and fig. 2C is an exponential smooth movement average line (long period EMA) of 30 periods of the respiratory Flow signal Flow in fig. 2A. As can be seen by comparing the exponential smooth movement average line of fig. 2B and 2C: the variation of the exponential smoothing movement average line (EMA) for 10 cycles is greater than the variation of the exponential smoothing movement average line (EMA) for 30 cycles, i.e., the exponential smoothing movement average line for shorter cycles is more susceptible to the respiratory Flow signal Flow than the exponential smoothing movement average line for longer cycles; meanwhile, when the respiratory Flow signal Flow has a large variation, the exponential smooth movement average line with a long period does not immediately reflect the variation of the respiratory Flow signal Flow, but is delayed. Therefore, the respiratory phase of the user is determined by using the exponential smoothing movement average line as the respiratory reference line, and most of noise can be filtered to maintain the stability of the respiratory phase determination signal, but at the same time, the longer period of exponential smoothing movement average line also causes the problem that the respiratory phase determination signal is distorted due to the real variation of the delayed response respiratory flow signal, which is particularly obvious when the respiratory system just leaks or just stops leaking, for example, the leaking occurs in a ventilation pipeline connecting the respiratory apparatus and the respiratory mask worn by the user.
Referring to fig. 3A and 3B, fig. 3A does not use the breathing reference line tracking acceleration method of the present invention, and when the ventilator system starts to leak air, fig. 3A shows the system breathing Flow (denoted as C11), the breathing Flow signal Flow (denoted as C12), and the breathing reference line (denoted as C13) of the long period EMA, wherein the breathing reference line (denoted as C13) of the long period EMA is not corrected by the breathing reference line reference correction value. Fig. 3B is a respiratory phase determination signal (denoted C14) with respect to a time axis generated according to fig. 3A, wherein the respiratory phase determination signal (denoted C14) has four values (1-4) on a phase axis corresponding to the four phases, respectively, so that the respiratory phase of the user has four phases.
In fig. 3A and 3B, the time axis is divided into 5 sections (or 5 stages) such as A1 to E1:
interval A1: the respiratory phase determination signal (labeled C14) may be triggered normally.
Interval B1: when the ventilator system begins to enter the air leakage state, the system respiratory Flow (labeled C11) rises suddenly, so that the respiratory Flow signal Flow (labeled C12) and the respiratory reference line (labeled C13) of the long-period EMA do not intersect at all, which causes a deviation in the respiratory phase determination signal (labeled C14).
Interval C1: the respiratory phase determination signal (labeled C14) cannot be triggered and the respiratory reference line (labeled C13) is tracked, wherein the respiratory phase determination signal (labeled C14) cannot be triggered, which means that the respiratory phase determination signal (labeled C14) stays at a respiratory phase exceeding a specified threshold time, and from the end of the interval B1 to the interval C1, the respiratory phase determination signal (labeled C14) stays at the respiratory phase 2, as shown in fig. 3B.
Interval D1: after a delay of about 12 respiratory cycles, the respiratory reference line (labeled C13) has been able to catch up with the respiratory Flow signal Flow (labeled C12) and reached a stage sufficient to initially determine the phase, but at this time the phase may deviate.
Interval E1: at this time, the respiratory phase determination signal (labeled C14) may be triggered normally, although the respiratory Flow signal Flow (labeled C12) is still high compared to the interval A1.
Referring to fig. 4A and 4B, fig. 4A does not use the breathing reference line tracking acceleration method of the present invention, and when the ventilator system starts to change from a leak to a leak, fig. 4A shows the system breathing Flow (denoted as C21), the breathing Flow signal Flow (denoted as C22), and the breathing reference line (denoted as C23) of the long period EMA, wherein the breathing reference line (denoted as C23) of the long period EMA is not corrected by the breathing reference line reference correction value, with respect to the time axis. Fig. 4B is a graph of the respiratory phase determination signal (labeled C24) generated with respect to the time axis according to the determination of fig. 4A.
In fig. 4A and 4B, the two sections are divided into 5 sections (or 5 stages) such as A2-E2:
interval A2: the respiratory phase determination signal (labeled C24) may be triggered normally.
Interval B2: when the ventilator system begins to enter a state of transition from a leak to a leak, the system respiratory Flow (labeled C21) is suddenly reduced such that the respiratory Flow signal Flow (labeled C22) and the respiratory reference line of the long period EMA (labeled C23) are completely disjoint, which causes a deviation in the respiratory phase determination signal (labeled C24).
Interval C2: the respiratory phase determination signal (labeled C24) cannot be triggered and the respiratory reference line (labeled C23) of the long period EMA is tracked.
Interval D2: after a delay of about 4.5 respiratory cycles, the respiratory reference line (labeled C23) of the long-cycle EMA has been able to catch up with the respiratory Flow signal Flow (labeled C22) and reached a phase sufficient to initially determine the phase, but the phase may deviate at this time.
Interval E2: the respiratory phase determination signal (labeled C24) may have been triggered normally.
Referring to fig. 5A and 5B, fig. 5A shows a system respiratory Flow (denoted as C31), a respiratory Flow signal Flow (denoted as C32), a respiratory reference line of a long period EMA (denoted as C33), and a respiratory reference line reference correction value (denoted as C35) with respect to a time axis when a ventilator system starts to leak air using the respiratory reference line tracking acceleration method of the present invention, wherein the respiratory reference line of the long period EMA (denoted as C33) is corrected according to the respiratory reference line reference correction value (denoted as C35) in a section C3. Fig. 5B is a graph of the respiratory phase determination signal (labeled C34) generated with respect to the time axis according to the determination of fig. 5A.
In fig. 5A and 5B, the sections can be divided into 5 sections (or 5 stages) such as A3 to E3:
interval A3: the respiratory phase determination signal (labeled C34) may be triggered normally.
Interval B3: when the ventilator system begins to enter the leak state, the system respiratory Flow (labeled C31) rises such that the respiratory Flow signal Flow (labeled C32) does not intersect the respiratory reference line of the long period EMA (labeled C33) at all, which causes a deviation in the respiratory phase determination signal (labeled C34).
Interval C3: the respiratory phase determination signal (labeled C34) cannot be triggered, and the respiratory reference line (labeled C33) of the long-period EMA is tracked and corrected according to the respiratory reference line reference correction value (labeled C35).
Interval D3: after a delay of about 2 respiratory cycles, the respiratory reference line (labeled C33) of the long-period EMA has been able to catch up with the respiratory Flow signal Flow (labeled C32) and reached a phase sufficient to initially determine the phase, but the phase may deviate.
Interval E3: at this time, the respiratory phase determination signal (labeled C34) may be triggered normally, although the respiratory Flow signal Flow (labeled C32) is still high compared to the interval A3.
Referring to fig. 6A and 6B, fig. 6A shows a system respiratory Flow (denoted as C41), a respiratory Flow signal Flow (denoted as C42), and a respiratory reference line (denoted as C43) of a long period EMA, wherein the respiratory reference line (denoted as C43) of the long period EMA is corrected according to the respiratory reference correction value (not shown) in a section C4 when the ventilator system starts to transition from a leak to a leak-free state by using the respiratory reference line tracking acceleration method of the present invention. Fig. 4B is a respiratory phase determination signal (denoted as C44) with respect to the time axis determined according to fig. 4A.
In fig. 6A and 6B, the sections can be divided into 5 sections (or 5 stages) such as A4 to E4:
interval A4: the respiratory phase determination signal (labeled C44) may be triggered normally.
Interval B4: when the ventilator system begins to enter a state of transition from a leak to a leak, the system respiratory Flow (labeled C41) is suddenly reduced such that the respiratory Flow signal Flow (labeled C42) and the respiratory reference line of the long period EMA (labeled C43) are completely disjoint, which causes a deviation in the respiratory phase determination signal (labeled C44).
Interval C4: the respiratory phase determination signal (labeled C44) cannot be triggered, and the respiratory reference line (labeled C43) of the long-period EMA is tracked and corrected according to the respiratory reference correction value (not shown).
Interval D4: after a delay of about 2.5 respiratory cycles, the respiratory reference line (labeled C43) of the long-cycle EMA has been able to catch up with the respiratory Flow signal Flow (labeled C42) and reached a phase sufficient to initially determine the phase, but the phase may deviate.
Interval E4: the respiratory phase determination signal (labeled C44) may have been triggered normally.
Referring to fig. 7 and 8, fig. 7 is a flow chart of the respiratory reference line tracking acceleration method of the present invention, and includes steps S1 to S5, corresponding to the flow chart of the respiratory reference line tracking acceleration method of the present invention shown in fig. 7, fig. 8 discloses a calculation module 20 of the respiratory reference line tracking acceleration method of another embodiment of the present invention, and compared with the calculation module 10 disclosed in fig. 1, fig. 8 further includes a modulation trigger condition determining unit 18, a first data switch to a fourth data switch 21-24, wherein an output end of the modulation trigger condition determining unit 18 is connected with a control end SW of the first to fourth data switches 21-24 to control data output of the first to fourth data switches 21-24, and the modulation trigger condition determining unit 18 is connected with the high and low point determining unit 12, the respiratory reference line unit 13, the amplitude determining unit 14, and the phase detecting unit 17 to receive output data of the high and low point determining unit 12, the respiratory reference line unit 13, the amplitude determining unit 14, and the phase detecting unit 17.
The first to third data switches 21 to 23 each have an input terminal, an output terminal and the control terminal SW for controlling whether the data of the input terminal can be outputted via the output terminal; the fourth data switch 24 has a control end SW, a first input end X, a second input end Y and an output end O, the control end SW can selectively output the data of the first input end X or the data of the second input end Y from the output end O, wherein the input end and the output end of the first data switch 21 are respectively connected to the amplitude determining unit 14 and the breathing reference value unit 15, the input end and the output end of the second data switch 22 are respectively connected to the high-low point determining unit 12 and the breathing reference value unit 15, the input end and the output end of the third data switch 23 are respectively connected to the breathing reference unit 13 and the breathing reference value correcting unit 16, the first input end X and the second input end Y of the fourth data switch 24 are respectively connected to the breathing reference unit 13 and the breathing reference value correcting unit 16, and the output end O of the fourth data switch 23 is connected to the phase detecting unit 17.
Referring to fig. 7 and 8, the steps S1 to S5 include:
step S1 (calculate relative high/low point): the high-low point determining unit 12 of the computing module 20 receives the respiratory Flow signal Flow from the respiratory signal unit 11 and generates and outputs the relatively high point PoleH accordingly n The relatively low point Polel n Wherein the foot code n represents the current value. The respiration reference line unit 13 also receives the respiration Flow signal Flow from the respiration signal unit 11, and generates and outputs a respiration reference line accordingly. The amplitude determination unit 14 receives the relatively high point PoleH from the high and low point determination unit 12 n The relatively low point Polel n And accordingly generates and outputs a respiratory amplitude FlowPP. Respiratory amplitude FlowPP calculation formulaThe method comprises the following steps:
·FlowPP n ＝PoleH n -PoleL n wherein the foot code n represents the current value.
Step S2 (whether the phase detection is timeout): when the phase detecting unit 17 of the computing module 10 calculates the respiratory phase determining signal according to the respiratory Flow signal Flow transmitted from the respiratory signal unit 11 and the respiratory datum value Base outputted from the respiratory datum unit 13 or the corrected respiratory datum value Bnew outputted from the respiratory datum correction unit 16 transmitted from the fourth data switch 24, and determines that the respiratory phase determining signal stays in a respiratory phase exceeding a time threshold (i.e. the respiratory phase determining signal is not triggered when timeout), the phase detecting unit 17 outputs a first correction signal (the value of which is true) to the modulation triggering condition determining unit 18, the Flow jumps to step S3, and when the phase detecting unit 17 determines that the respiratory phase determining signal stays in a respiratory phase not exceeding the time threshold (i.e. the respiratory phase determining signal is not triggered when timeout has not occurred), the Flow jumps to step S1. Wherein the time threshold may be, for example, an average of the cycle length of the first 30 respiratory cycles of 0.01-0.99.
Step S3 (whether or not the modulation trigger condition is satisfied): the modulation trigger condition judgment unit 18 judges the modulation trigger condition based on the relative high point PoleH received from the high and low point judgment unit 12 n 、PoleH n-1 And the relatively low point PoleLn and PoleL n-1 And the respiratory reference line values Basen, basen-1 received from the respiratory reference line unit 13 and the respiratory amplitude FlowPP received from the amplitude determination unit 14 n 、FlowPP n-1 And the first correction signal received from the phase detection unit 17, to determine whether the modulation trigger condition is satisfied, wherein a respiration amplitude threshold Th pp A respiratory high point threshold Th H A respiratory depression threshold Th L And a respiratory datum threshold Th BL First, it is calculated that the modulation trigger condition is satisfied when any one of the following trigger conditions is satisfied and the value of the first correction signal is true, where the foot code n represents the current value and the foot code n-1 represents the previous value:
amplitude modulation trigger condition: (FlowPP) n -FlowPP n-1 )＞Th pp
Gao Dian modulation trigger condition: (PoleH) n -PoleH n-1 )＞Th H
Low point modulation trigger condition: (Polel) n -PoleL n-1 )＞Th L
Baseline modulation trigger condition: (Base) n -Base n-1 )＞Th BL
Wherein the respiratory amplitude threshold Th pp The respiratory high point threshold Th H The respiratory depression threshold Th L And the respiratory reference line threshold Th BL The calculation formulas of (a) are respectively as follows:
·Th pp ＝FlowPP n-1 ×Pth pp the respiratory amplitude threshold parameter Pth pp Between 1% and 200%;
·Th H ＝FlowPP n-1 ×Pth H the high-point threshold parameter Pth H Between 1% and 200%;
·Th L ＝FlowPP n-1 ×Pth L the low point threshold parameter Pth L Between 1% and 200%;
·Th BL ＝FlowPP n-1 ×Pth BL the datum line threshold parameter Pth BL Between 1% and 200%.
When the modulation trigger condition judging unit 18 judges that the modulation trigger condition is met, the output end of the modulation trigger condition judging unit 18 outputs a control signal to the control ends SW of the first to fourth data switches 21-24 to control the data output of the first to fourth data switches 21-24 so that the respiratory reference line reference value unit 15 can receive the relatively high point PoleH transmitted from the high and low point judging unit 12 n The relatively low point Polel n The respiratory amplitude FlowPP transmitted from the amplitude determination unit 14 n And the respiratory datum line correction unit 16 can receive the respiratory datum line value Base transmitted by the datum line unit 13 n At the same time, the phase detection unit 17 is changed fromThe breathing reference line correction unit 16 receives the corrected breathing reference line value without the breathing reference line value being received by the breathing reference line unit 15, the flow jumps to step S4, and when the modulation trigger condition judgment unit 18 judges that the modulation trigger condition is not established, the flow jumps back to step S1.
Step S4 (calculate respiratory reference line reference value): the respiratory reference line reference value unit 15 is based on the relatively low point PoleL received by the high and low point determination unit 12 n And the respiratory amplitude FlowPP received by the amplitude determination unit 14 n-1 Calculate a reference value Bref of respiratory datum line n Wherein the foot code n represents the current value, the foot code n-1 represents the previous value, and the respiratory reference line refers to the value Bref n The calculation formula of (2) is as follows:
·Bref n ＝PoleL n +FlowPP n-1 ×P ref the datum line reference value parameter P ref Between 1% and 99%.
Step S5 (correct respiratory reference line): the respiratory reference line correction unit 16 corrects the respiratory reference line based on the respiratory reference line reference value Base received by the respiratory reference line unit 13 n-1 And the respiratory reference line reference value Bref received by the respiratory reference line reference value unit 15 n Calculating a corrected respiratory baseline value Bnew n The respiratory reference line correction unit 16 corrects the corrected respiratory reference line value Bnew n Output to the phase detection unit 17 via the fourth data switch 24, wherein the foot code n represents the current value, the foot code n-1 represents the previous value, and the corrected respiratory baseline value Bnew n The calculation formula of (2) is as follows:
·Bnew n ＝(Bref n -Base n-1 )×P BL +Base n-1 the reference line modulates parameter P B， Between 1% and 99%.
The respiratory amplitude threshold parameter Pth in fig. 5A, 5B, 6A, and 6B pp The high-point threshold parameter PthH, the low-point threshold parameter Pth L And the baseline threshold parameter Pth BL The datum line reference value parameter P ref The datum line is adjustedVariable parameter P BL The values of (2) are 50%.
In fig. 5A, 3 relatively high points PoleH such as point P2, point P4, point P6, etc. and 3 relatively low points PoleL such as point P1, point P3, point P5, etc. are also marked, wherein point P1 and point P2 are in a normal state, the change of point P4 (compared to point P2) establishes a modulation trigger condition (i.e., a high point modulation trigger condition), so the calculation module 20 starts tracking and at the next point (point P5), updates the breathing reference value (as indicated by C35) and accordingly corrects the breathing reference (as indicated by C33), then the change of point P5 (compared to point P3) establishes a modulation trigger condition (i.e., a low point modulation trigger condition), so the calculation module 20 updates the breathing reference value again (as indicated by C35) and accordingly corrects the breathing reference (as indicated by C33), and then the corrected breathing reference (as indicated by C33) can catch up with the breathing Flow signal (as indicated by C32), and then the breathing phase determination signal (as indicated by C34) can be triggered normally.
As can be seen from the above description of fig. 8: the computing module 20 of fig. 8 has similar functions as the computing module 10 of fig. 1 when the modulation trigger condition is met, but the computing module 20 of fig. 8 is not the same as the computing module 10 of fig. 1 when the modulation trigger condition is not met. Furthermore, all the constituent units in fig. 8, such as the respiratory signal unit 11, the..the modulation trigger condition judging unit 18, and the first to fourth data switches 21 to 24, may be configured by hardware, software, or a combination of hardware and software. Similarly, all the constituent units in fig. 1 may be hardware, software, or a combination of hardware and software.
Comparing fig. 3A and fig. 5A, the breathing reference line tracking acceleration method of the present invention can greatly shorten the time for tracking the breathing reference line from 12 breathing cycles to 2 breathing cycles, and similarly comparing fig. 4A and fig. 6A, the breathing reference line tracking acceleration method of the present invention can greatly shorten the time for tracking the breathing reference line from 4.5 breathing cycles to 2.5 breathing cycles. Therefore, the respiratory datum line tracking acceleration method can achieve the purpose of rapidly adjusting the respiratory datum line.
The present invention is not limited to the above-described preferred embodiments, but is intended to be limited to the following description, and any modifications, equivalent changes and variations in the above-described embodiments according to the technical principles of the present invention will fall within the scope of the present invention, as long as they do not depart from the scope of the present invention.
Claims (5)
1. A respiratory datum line tracking acceleration method is characterized by providing a calculation module and receiving a respiratory flow signal, and comprises the following steps:
step S1: the calculation module generates a respiratory amplitude and a respiratory datum line according to the respiratory flow signal;
step S2: the calculation module generates a respiratory phase judgment signal according to the respiratory flow signal and the respiratory datum line, when the respiratory phase judgment signal stays at a respiratory phase exceeding a time threshold, the flow jumps to step S3, and when the respiratory phase judgment signal stays at a respiratory phase not exceeding the time threshold, the flow jumps back to step S1;
step S3: judging whether a modulation triggering condition is met, if so, jumping to the step S4, and if not, jumping back to the step S1;
step S4: the calculation module generates a respiration datum line reference value according to the product of the respiration amplitude and a proportional parameter and a relatively low point in the respiration datum line;
step S5: the calculation module corrects the breathing datum line according to the breathing datum line reference value;
wherein, the establishment of the modulation trigger condition means that any one of the following trigger conditions is established:
amplitude modulation triggering conditions: the difference between two consecutive breath amplitudes in the breath baseline is greater than a breath amplitude threshold;
high point modulation trigger conditions: the difference between two consecutive relatively high points in the respiratory datum line is greater than a respiratory high point threshold;
low point modulation trigger conditions: the difference between two consecutive relatively low points in the respiratory datum is greater than a respiratory low point threshold;
baseline modulation triggering conditions: the difference between two consecutive points in the respiratory reference line is greater than a respiratory reference line threshold.
2. The method of claim 1, wherein each of the respiration amplitude threshold, the respiration high point threshold, the respiration low point threshold, and the respiration baseline threshold is a product of a respiration amplitude generated by the computing module according to the respiration flow signal and a proportional parameter.
3. The respiratory baseline tracking acceleration method of claim 1, wherein the respiratory flow signal is a real-time measured flow signal, a filtered flow signal, or a patient respiratory signal obtained by processing the measured signal.
4. The respiratory baseline tracking acceleration method of claim 1, wherein the respiratory baseline reference value is calculated by:
the respiratory datum reference value Bref n ＝PoleL n +FlowPP n-1 ×P ref The datum line reference value parameter P ref Between 1% and 99% Polel n To be the current relatively low point in the respiratory baseline, flowPP n-1 For the previous respiratory amplitude in the respiratory baseline, wherein foot code n represents the current value and foot code n-1 represents the previous value.
5. The respiratory baseline tracking acceleration method of claim 4, wherein the modified respiratory baseline value is calculated according to the formula:
the corrected respiratory datum line value Bnew n ＝(Bref n -Base n-1 )×P BL +Base n-1 The reference line modulating parameter P BL Between 1% and 99% Base n-1 Is the previous value of the respiratory datum line.
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